Automatic elasto-valvular hypodermic sampling needle

ABSTRACT

A novel blood-drawing device with automatically actuatable elasto-valvular mechanism or component, sensitive to pressure differential changes, attaining variable aperture sizes in the opening phase aimed to reduce mechanical hemolysis of the red blood cells and other cellular disintegration caused by high shear forces, and, achieving a normally closed position to prevent blood drip; a valve is situated between a pair of preformed internal chambers or cavities that separate two axially arranged sharpened cannulas; the device with a preferably transparent hub for visual indication of the functional capabilities of the device, the hub transparency being important during effective extraction of singular as well as several separate fluid samples such as venous blood collectible into one or more evacuated sample tubes, respectively, during a single venipuncture; such device packaged in sterile condition and made to be disposable after a singular use.

nite States Patent 91 [111 3,848,579 Villa-Real Nov. 19, 1974 1 AUTOMATIC ELASTO-VALVULAR 129,280

HYPODERMIC SAMPLING NEEDLE [76] Inventor: Antony-Euclid Villa-Real, 5934 Schering Rd., Baltimore, Md. 21206 [22] Filed: Feb. 23, 1973 [21] Appl. No.: 335,419

[52] US. Cl. 128/2 F, 128/276, 128/218 NV [51] Int. Cl. A6lb 5/14, A6lm 5/32 [58] Field of Search 128/2 F, DIG. 5, 214 R, l28/2l4.4, 221, 218 N, 350 V, 274, 218 NV, 276; 137/525, 525.1, 5253; 251/120, 121

[5 6] References Cited UNITED STATES PATENTS 1,607,993 11/1926 Loewy 128/274 UX 2,897,835 8/1959 Philippe 137/525.l X 2,941,544 6/1960 Peras 137/525 3,089,490 5/1963 Goldberg 128/218 NV 3,091,240 5/1963 McConnaughey 128/218 NV 3,245,428 4/1966 Klimak et a1. l37/525.1 X 3,295,547 1/1967 Scaramucci 137/315 3,301,443 l/l967 Clancy et a1 l37/525.l X 3,557,778 l/l97l Hughes 128/2 F 3,659,587 5/1972 Baldwin.... l28/D1G. 5 3,710,794 1/1973 Shields 128/218 NV FOREIGN PATENTS OR APPLICATIONS 1,278,387 10/1961 France 128/D1G. 5

5 Primary Examiner-Richard A. Gaudet Assistant Examiner-J. C. McGowan A novel blood-drawing device with automatically actuatable elasto-valvular mechanism or component, sensitive to pressure differential changes, attaining variable aperture sizes in the opening phase aimed to reduce mechanical hemolysis of the red blood cells and other cellular disintegration caused by high shear forces, and, achieving a normally closed position to prevent blood drip; a valve is situated between a pair of pre-formed internal chambers or cavities that separate two axially arranged sharpened cannulas; the device with a preferably transparent hub for visual indication of the functional capabilities of the device, the hub transparency being important during effective extraction of singular as well as several separate fluid samples such as venous blood collectible into one or more evacuated sample tubes, respectively, during a single venipuncture; such device packaged in sterile condition and made to be disposable after a singular use.

ABSTRACT 31 Claims, 29 Drawing Figures 2 u. 30 r /4 44 [42 Q6 7/1932 Germany 128/D1G. 5

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SHEEF 4 OF 6 mw ww MN ON K kw PATENTEQQBV I QIBM sum 5 or s AUTOMATIC ELASTO-VALVULAR HYPODERMIC SAMPLING NEEDLE BACKGROUND OF THE INVENTION Before proceeding into the depths of the historical background of the invention, it is imperative that the essentials of the VACUTAINER SYSTEM of blooddrawing be substantially explained in order that clarification on the subject may be better achieved.

Fundamentally, the VACUTAINER SYSTEM re quires the following basic items:

1. One or more VACUTAINER tubes. Each tube is a self-aspirating specimen collector and container that is generally made of transparent glass. One end of the tube is closed by the glass structure itself, while the other end is plugged by a flanged rubber stopper. Each VACUTAINER tube had been preevacuated of its internal gaseous contents so that we can refer to it as a pre-evacuated sample tube. It is, considerably, physically empty, and that this condition creates a favorably effective negativity of pressure which provides the VACUTAINER tube with an excellent power for aspirating fluidic specimens such as blood samples when used in coordination with the aforementioned VACU- TAINER SYSTEM.

2. A VACUTAINER HOLDER which is preferably constructed of rigid plastic material, having a tubular shape, open at its entrant end, and, accommodating within the tubular limits of its internal diameter the external circular borders of even the largest utilizable VACUTAINER tube used for this particular purpose. Each collecting tube can slidably be engaged or disengaged, one at a time, within the tubular extent of the barreled holder, allowing each vial to be interconnected with, or disconnected from the hind portion of the cannula. The other end of the VACUTAINER HOLDER provides a closure with a central external enlargement having an axially running screw threaded bore that furnishes a suitable means through which the correspondingly adaptable screw form part of the axially alignable hypodermic needle can be firmly attached.

3. A hypodermic needle that has two beveled ends-the forward beveled end and the rearward beveled end; the former having been designed for the purpose of puncturing the skin and the immediate underlying tissues including the vein, and the latter, utilizable for the penetration of the diaphragmatic area of the rubber stopper that plugs each VACUTAINER tube. With this arrangement, it follows that, after the forward beveled end has made the correct penetartion of the vein, and the rearward beveled end had completely pierced the diaphragm of the said rubber stopper, a resultant physical continuity is created between the flowing venous blood on one side, and the aspirating vacuum on the opposite side through the common bore of the cannula. This is the reason why the blood specimen gets collected into the VACUTAINER tube, sourced from the venous side.

4. A fluid source such as venous blood source with which the hypodermic needle is connected in relation to the evacuated sample tube.

When the VACUTAINER SYSTEM for blood specimen extraction was first introduced in the field of Laboratory Medicine, the applicable hypodermic needles used during that time were not equipped with structural and functional means of controlling the blood flow from the vein through each hypodermic needle. This situation caused some unavoidable blood drip or spatter during inter-tubular substitution due to the fact that within such span of time when one collection tube was disengaged from its connection with the hypodermic needle and then replaced by the next preevacuated sample tube in line, the absence of a blocking factor that could have prevented the bore-continuity between the venous side and the ambient environment, propagated the inter-linkage of the pressure differential existing between the venous side and the ambient condition. This was because the hypodermic needle was still connected with the vein during the process of inter-tubular changing as in the case of multi-sampling of blood with a single venipuncture. Some quantities of dripping blood used to accummulate at the basal sector of the plastic VACUTAINER HOLDER. Moreover, due to the physical motions relevant to the many entries and exits of the plurality of collection tubes, each one being individually engaged into and then disengaged out of the plastic VACUTAINER HOLDER, the accummulated blood inside the holders barrel were oftentimes spilled out, messing the patients or donors arm, clothing or even the hospital bed linens.

In the latter part of the 1960s, Becton, Dickinson and Company of Rutherford, NJ. introduced a modified version of the said hypodermic needle, an improved kind which was designed more specifically for multisample collection of blood specimens. This hypodermic needle has a tubular rubber sleeve that snugly fits around the hind portion of the cannula. This sleeve envelops the external area of that said portion of the cannula and covering the laterally situated hole found just a little measure from the hindmost piercing portion of the device.

During the filling phase, the lateral hole is uncovered by the rubber sleeve that has been pushed forward by the rubber stopper of the VACUTAINER tube. Hence the said lateral hole comes in direct communication with the vein through the common bore of the cannula, thereby, blood is aspirated automatically into the connected collection tube. However, when the desired amount of specimen has been collected into the said tube, and such vial has now been pulled away from its needle connection, the temporarily compressed rubber sleeve springs back to attain its orriginal lengthwise hole-covering position. As a result, it becomes evident that during the time span existing between intertubular replacement, the lateral hole becomes actually plugged from exposure to the ambient environment. Because of this feature, the blood drip is prevented from occurring during the process of multi-sampling of blood involving a single venipuncture.

Recently, Becton, Dickinson and Company made another modification of their MULTIPLE-SAMPLE HY- .PODERMIC NEEDLE centering the innovative dripthat, such closure comprising of rubber material is thinly constructed and easily puncturable'by the hind beveled part of .the cannula. Relatively, however, the

governing principle involved in this version is about the same as compared to that of the preceding version.

Although the two improved versions are capable of preventing the undesired blood drip, there is an inherent chief disadvantage: There is a considerable resistance exerted by the tubular rubber sleeve against the forwardly pushed ramming mass of rubber stopper of the collection tube. The only way this resisting force of the said tubular rubber sleeve could be overcome is by pushing comparatively harder at the base of the collection tube with the thumb or with the palm of the hand, and then, maintaining that firm pushing action to prevent the rebound of the temporarily compressed elastic tubular sleeve. If this firm push at the base of the said tube is not maintained, there arises a danger of displacing the rubber stopper a bit rearwards, a condition which may bring forth blocking of the cannular hole that communicates with the vacuum of the collection tube, and then resultant inhibition of blood flow into the collecting vial could happen thereby interrupting the process of blood sampling. Even though it can be argued that, in the performance of such mechanical manipulation, the operator can adjust to the additional manual requirement, still, from the viewpoint of ease of operation, the aforementioned hypodermic needles produced by Becton, Dickinson and Company can be considered crude to operate. Additionally, granting that the other hand can aid the manipulation in an effort to stabilize the needles positionintravenously, the extra-strenous requirement may possibly alter the optimal location of the said needle in relation to the said vein. Aside from this, the initial quick forward push exerted upon the VACUTAINER tube in order to effectively compress the elastic tubular structure of the rubber sleeve so as to shrink its lengthwise occupancy of the exterior surfaces of the hind portion of the cannula, may be inefficiently transmitted to the forward beveled end of the hypodermic needle; such undesired forcetransmission when not effectively balanced by a corresponding magnitude of counter-force exerted by the other hand, may essentially cause a dual venous-wall puncturing, culminating to a greater injury upon the somatic constitution of the blood vessel including the immediate surrounding tissues.

Lately, there is another kind of multi-sample hypodermic needle produced by MPL called QUICK- DRAW. Its ruling feature is the use of a two-part cannula-the front-part cannula which is stationary, and the rear-part cannula which can slide back and forth in a longitudinally directed fashion, thereby providing a means to effect an inter-cannular bore physical engagement or disengagement as the longitudinally movable rear cannulas frontal section alternately pierces and unpierces an intermediary rubber plate at the central site of the said plates material break. Once the beveled section of the front-part cannula has made the right venous penetration and has been correctly positioned inside the lumen of the vein, the rear-part cannula is then pushed forward slideably by the mass of the forwardly directed rubber stopper of the VACUTAINER tube. As a result, the frontal sector of the rear-part cannula pierces the intermediary rubber plate at its material break. This situation brings forth a resultant blood flow from the venous side propagated through the cannular bores of both the front-part and the rear-part cannulas soon as the rubber stopper of the said tube has been substantially penetrated by the rearward beveled edge of the rear-part cannula. Having thus achieved a physical continuity between the venous side and the vacuum of the collecting vial, blood specimen is then transported into the said container.

Afterwards, as the blood-filled tube in withrawn from its connection with the rear-part cannula, the movable feature of such rear cannular part this time enables it to move along the rearward direction of the now-beingdisengaged rubber stopper while still being pierced by that rear cannular part, until the rearmost slideability limitations of the rear-part cannulas has been reached, at which point, the rubber plate becomes completely unpierced by the said frontal sector of that rear-part cannula, and that, the material break of the rubber plate attains its normally close position, thus blocking blood flow from the venous side. This is how blood drip is prevented during intertubular replacement of collection tubes.

Despite the fact that the principle of operation of the QUICK-DRAW HYPODERMIC NEEDLE has deviated from the use of the rubber sleeve which causes the disadvantages mentioned before the device poses another type of inferiority because of its unstable functional feature derived from the manually operable movable rear-part cannula. Its instability during the course of multi-sampling, somehow negatively affects the dexterity of the operator, and, such a device pre-disposes the blood sample to a greater danger of cellular destruction as an after-effect of the slideability of the rear-part cannula due to the mechanical impact between the said rear-part cannula and the other component structures of the device, while blood is being transported through such medium.

From the point-of-view of analytical relativistics involving the governing principles of the correlative link between the in-vivo and in-vitro hemodynamics occurring during multi-sampling, to actual utilization of the constant aperture size characteristics of both the Beeton-Dickinson and the MPL types of hypodermic needles, clearly reveal the lack of structural adaptability in reducing the detrimental high shear forces encountered during the initial filling phase. On the basis of this finding, the use of those hypodermic needle versions predisposes the blood specimen to a higher degree of hemolysis and other cellular disintegration constituting an inevitable disadvantageous aftermath.

The above-mentioned hypodermic needle versions are not equipped with any visual indicator which would enable the operator to correctly determine whether or not the desired blood flow from the vein through the cannula had already ensued. The absence of such a visual indicator will, at times, result in a trial-and-error premature exposure of the vacuum contained within the collection tube. Since the aspirating power of the VACUTAINER tube is directly proportional to the degree of vacuum or negativity of pressure contained therein, the improper location or wrong angular positioning of the front beveled end of the hypodermic needle in relation to the actual lumen of the vein can result in some loss of the pre-evacuted vials aspirating power.

BRIEF SUMMARY OF THE INVENTION This invention pertains to a novel blood-drawing device particularly utilizable for the effective extraction of either singular volume or several quantities'of separate blood samples collectible into one or'more evacuated sample tubes, respectively, and achieving an advantageous reduction of mechanical hemolysis of the red blood cells as well as possibly decreasing the danger of disintegration of other cellular elements suspended in the plasma caused by high shear forces in conjunction with the use of pre-evacuated sample tubes, and, at the same time allowing the convenient multisampling of blood, attainable with a single venipuncture and without resulting in blood drip or spatter; said new device provided with a built-in automatically actuateable elasto-valvular mechanism or component with special configurations and other valvular characteristics and properties pre-tested to achieve gradations of reactive sensitivity to pressure differential changes that trigger, in a much more automatic fashion, the opening and closing responses of such valve; said elasto-valvular component situated in between a pair of internal chambers or pre-formed cavities that separate the longitudinally aligned pair of front and rear cannulas-the front cannula utilizable for the penetration of the relevant bodily tissues for the purpose of establishing a physical connection with the venous blood source or other fluid sources, and, the rear cannula aimed for the proper puncturing of the rubber stopper plugging each evacuated sample tube, thereby providing means for communication between the said evacuated sample tube and the internal parts of the said device, as well as affording a physical continuum with the venous blood source; said pair of chambers or cavitations called the fore and the aft cavities are within the internal confines of a strong and rigid and preferably transparent plastic hub means, holding the stationary margins of the said elasto-valvular component firmly in place, and, at the same time, such hub means fixing the inner portions of the front and the rear cannulas in an inflexibly and straightly aligned position; said front and rear cannulas preferably made of metallic composition, described as stationary with respect to their attachements with the hub means, such front and rear cannulas having bore diametric dimensions less than the diametric dimensions of both the fore and aft cavities; said elastovalvular mechanism or component attaining variability in valvular apertural sizes during the opening phase of the said device to enhance an adjustable means of reducing the stressful high shear forces inherently encountered during the use of evacuated sample tubes, and, with the provision of the streamlined edges characterizing the elasto-valvular components valvular configurations through which or around which blood rushes, cell destruction of the red blood cells,.the white blood cells and possibly the platelets, are considerably reduced. The aperture sizes of the valve are relative to the degree of pressure diffferentials between the venous blood source and the aspirating evacuated sample tube in correspondingly direct proportionality to one another in each pair of conditions, after the initial opening peak has been achieved. In the normally closed position, the said elasto-valvular mechanism achieves its efficient role in preventing the transport of the blood quantities across it due to the inherent prevalvular stiffness. As for example, a considered weak' pressure differential that cannot open the valve is the pressure differential existing between the precalculated range of venous pressures varying from individual to individual, and, the range of allowable atmospheric pressures varying according to depth as well as height relative to sea level pressure. This feature, therefore, positively prevents the occurrence of blood drip from the venous side into the ambient environment while the needle is connected with the lumen of the said vein; such prevention of blood drip being specifically important firstly prior to the installation of the initial pre-evacuated sample tube, and secondly during the span of time while changing one blood-filled tube with another unused one until several tubes, in sequential order, have collected the necessary amounts of separate quantities of blood specimens during the process of multi-sampling involving s single venipuncture. This new type of hypodermic needle being provided with a preferably transparent hub for visual indication purposes; said device having certain finger-grippable exterior surface contours for its easy installation and disengagement with the corresponding inter-linking part of the VACUTAINER TUBE HOLDER; said device having a rear externally threaded screw form or other locking means adaptable to firmly link it, in a stable fashion, with the VACUTAINER TUBE HOLDER; said device being simple in construction can be economically massproducible; said device attaining medical praiseworthiness through the maintenance of a clinically presterilized condition in packaging; said device to be made disposable after a single use to avoid crosscontamination.

Basing on the preceding descriptions of this novel device centered upon its unique structural construction and functional capabilities abiding with the sound principles of Biophysics and Design Engineering, the following objects of the present invention are hereby discussed:

One object is to avail several designs or models of the new kind of hypodermic needle, which by virtue of the advantangeous structural designs and detailed internal configurations would facilitate the drawing of singular sample as well as multisample collection of blood specimens to be contained into a plurality of VACU- TAINER tubes, offering a relative ease on the performance of the technologist, technician, nurse or physician during the execution of the proper method of intratubular blood specimen filling.

Another object is the provision of a novel means to effect an automatic blood specimen flow and control of such flow within the said device by the use of a built-in elasto-valvular mechanism or component that can bring forth the efficient inter-tubular substitution of VACUTAINER tubes during multi-sample collection of said specimens without blood drip or spatter.

From the biophysical viewpoint, another object is to procure a much more adaptable device characterized by having a better capability of achieving a more flexible range and degree of aperture size variability as effected by the proper functional responses of the elastovalvular component relative to the pressure differential gradients existing between the venous pressure on one side and the aspirating vacuum of the VACUTAINER tube, on the other side. This actuateable variability in aperture size accomplished in a more streamlined and automatic fashion, will greatly eliminate the hemolysis of red blood cells as well as possibly prevent the disintegration of other cellular elements suspended in the plasma during the whole bloods passage through the poly-sample hypodermic needle.

A further object is to endure a greater possibility of diminishing the occurrence of venous wall collapse that happens more predominatly with the use of the currently manufactured hypodermic needles applicable to the VACUTAINER SYSTEM of drawing blood. Again, from the biophysical standpoint, this object may be carried out well because of the gradual opening characteristics of the elasto-valvular component during the first phase of vacuum-triggered fluidic-mass transport of the blood volume from the vein into the aspirating system, thus affording a less abrupt shock-wave propagation as compared to the constant aperture size of the current hypodermic needles that do not have a shockabsorbing mechanism.

Another object, specifically those designs that are each made of a transparent hub or main supporting part, is to provide the operator with some visual means inherent in their structural constitutions so as for him to effectively tell whether or not the favorable blood flow from the vein has already ensued through the front cannula and into the fore cavity of the main supporting part before he exposes the vacuum of the first VACU- TAINER tube. This feature would prevent the premature exposure of the negativity of pressure of the said first collecting container. With the transparency of the main supporting part, moreover, it would permit the operators visual knowledge about the functional efficiency of the eIasto-valvuar mechanism during the collection of blood samples.

Still a further object is to present a more-superior hypodermic needle in the light of enhancing greater automaticity of operation while offering a steadier device to handle as compared to the other hypodermic needles used in the field. This advantage highly diminishes the patient's or donors pre-disposition to the multilating physical injuries to the venous wall and the surrounding tissues that result in unsightly extravasation of blood, a condition which is sometimes encountered more preva- Iently and in a more extensive degree with the utulization of the cruder, in fact, partially mechanically manipulated inferior hypodermic needles used these days.

BRIEF DESCRIPTIONS OF ILLUSTRATIVE DRAWINGS In accordance with the primary and secondary aims of the present invention as a more superior innovation over the currently used ones, reference is made to the accompanying illustrative embodiments in the form of the following sequence of drawings that are labeled with specific numerals, letters, and numeral-letter combinations from which a more in-depth and thorough understanding of the novel features and advantages will be apparent. In the drawings:

FIG. 1 is an enlarged longitudinal section of Model A of the invention.

FIG. 2 is an enlarged longitudinal section of Model B of the invention.

FIG. 3 is an enlarged longitudinal section of Model C of the invention.

FIG. 4 is a more magnified longitudinal section in fragmentary form centering on the middle fundamental components of the Model A of the invention.

" F IG. 5 is another more magnified longitudinal section.

in fragmentary form of the Model C of the invention focussing on the middle important features.

FIG. 6 is an enlarged central cross-sectional view of Type 1 of the elasto-valvular mechanism or component.

FIG. 7 is an enlarged central cross-sectional view of Type II of the elasto-valvular mechanism or component.

FIG. 8 is an enlarged central cross-sectional view of Type III of the elasto-valvular mechanism or component.

FIG. 9 is an enlarged end view of the elasto-valvular mechanism or component of the Type I shown in FIG. 6.

FIG. 10 is an enlarged end view of the elasto-valvular mechanism or component of the type II shown in FIG. 7.

FIG. 11 is an enlarged front view of the elastovalvular mechanism or component of the Type III shown in FIG. 8.

FIG. 12 is an enlarged pictorial illustration of the relationship between the blood flow and control of such flow, the vein, the presently applied for poly-sample hypodermic needle shown attached to the plastic VACU- TAINER HOLDER all of which are drawn in central longitudinal views in an inter-connecting fashion. The VACUTAINER tube is drawn in a side elevational view and unattached to the hypodermic needle.

FIG. 13 is a much more magnified pictorial illustration of the relationship between the blood flow and control of such flow, the vein, the poly-sample hypodermic needle which is attached to the VACUTAINER HOLDER shown only in its frontal fragmentary form. All these basic components are drawn as interconnected to one another and shown in the central longitudinal sectional view.

FIG. 14 is another enlarged pictorial illustration of the relationship between the blood flow and the propa-' gation of such flow, the vein, the poly-sample hypodermic needle attached to the VACUTAINER HOLDER. All these important components are drawn in an interconnected central longitudinal sectional view. Here the VACUTAINER tube is shown properly engaged in the aspirating position, wherein the diaphragm of the rubber stopper plugging the said VACUTAINER tube has been pierced correctly by the hind portion of the rear cannula. The said tube is presented as partly drawn in the central longitudinal sectional view and partly in the side elevational view.

FIG. 15 is another enlarged pictorial illustration of the relationship between the blood flow and the inhibition or stopping of such continous flow within the device without removing the hypodermic needles intravenous engagement, and, without resulting in an undesirable blood drip or spatter even though the filled-in sample tube had already been pulled away from its connection with the rear cannula. The elasto-valvular mechanism or component is shown in the closed position and the poly-sample hypodermic needle is still firmly installed with the internally threaded bore of the tube holder.

FIG. 6 is a side elevation drawing of a typical VACU- TAINER tube that has been pre-evacuated and ready to be substituted into the barrel of the VACUTAINER HOLDER as soon as the preceding blood-filled collection tube has been completely cleared away'from the barreled holder.

FIG. 17 is another side elevation drawing-of an unused VACUTAINER tube, next in line and to be utilized during the process of venous blood multisampling.

FIG. 18 is an enlarged end view of the elasto-valvular mechanism or component of the Type I shown in FIG. 9, but this time, the valvular lips are in the open position. Surrounding its outermost circumference is a circular cross-section of the enveloping main supporting transparent plastic material.

FIG. 19 is an enlarged end view of the elasto-valvular mechanism or component of the Type II as shown in FIG. 10. However, the valvular lips are now illustrated in the open position. Fitted around the outermost circumferential border of the elasto-valvular structure is an enveloping cross-section of the main supporting transparent plastic material.

FIG. 20 is an enlarged frontal view of the elastovalvular mechanism or component of the Type III as shown in FIG. 11. Instead of the valvular lips drawn in the normally closed fashion, they are illustrated in the open position.

FIG. 21 is an enlarged central longitudinal sectional view of still another kind of poly-sample hypodermic needle herein designated as the Model D of the present invention.

FIG. 22 is a much more magnified central longitudinal sectional view of the Model D poly-sample hypodermic needle that is in the continously aspirating position. The hypodermic needle is also shown as interconnected with the VACUTAINER HOLDER, and, having completely pierced the diaphragm of the rubber stopper plugging the collection tube with the rear cannulas hindmost sharpened edge, while on the forward side, part of the front cannula is shown in the correct intra-venous position. The front cannula, the rear cannula, the VACUTAINER HOLDER and the VACU- TAINER tube are all drawn in the longitudinal section, and, partially in fragmentary form. The vein is illustrated in longitudinal section with the blood sample flowing from the venous lumen through the relevant internal structures of the hypodermic needle, and then transported into the evacuated collection tube.

FIG. 23 reveals an enlarged end view of the elastovalvular mechanism or component of the Type IV which is shown in the close position. Enveloping the outermost borders of the said component is a crosssection of the main supporting material made of plastic composition.

FIG. 24 illumines an enlarged end view of the elastovalvular mechanism or component of the Type IV as shown in FIG. 23, but this time the valvular lips are shown in the open position. Like FIG. 23, the enveloping main supporting transparent material is seen fitted around the elasto-valvular component.

FIG. 25 is an enlarged cross-sectional view taken from lines 30 and 30 along the direction of arrow m and m of FIG. 21.

FIG. 26 is an enlarged cross-sectional view taken from lines 32 and 32 as seen along the direction of arrows q and q of FIG. 21.

FIG. 27 is an enlarged cross-sectional view taken from lines 34 and 34 as perceived along the direction of arrows s and s of FIG. 21.

FIG. 28 is an enlarged central longitudinal section, partly in fragmentary form, of another alternative version of the same invention, herein assigned as the Model E, and, focussing on still a further type of elastovalvular mechanism or component known as the Uni- Lip Elasto-Valve Type V. The drawing illustrates the elasto-valvular mechanism or. component in both its close and open position.

FIG. 29 is an enlarged central longitudinal section, partly in fragmentary form, of a sixth version of the poly-sample hypodermic needle, herein designated as the Model F, and, centering on a sixth possible type of elasto-valvular mechanism or component called the Mono-Oval Elasto-Valve Type VI which is illustrated in both its close and open positions.

DETAILED DESCRIPTIONS ln FIGS. 1, 2 and 3, the following numerals and letters refer to specifically detailed parts of the first three models of the Euclidean Automatic Elasto-Valvular Poly-Sample Hypodermic Needle.

Numeral 1 is the frontal beveled end of the front cannula that is useful for the proper penetration of the skin and the immediate underlying tissues, as well as the wall of the blood vessel preferably a vein, 2 is the exposed extension or shaft of the front cannula, 3 is the bore that runs axially through the front cannula. The rear part of 2 designated as 4 is centrally and firmly held in the straight position by the front segment 6 of the main supporting material, 5 is the rearmost extent of the axially running bore 3 of the front cannula, 6 partially supports the elasto-valvular component 8 and internally having a centrally located cavity X that borders between 5 and 8; 7 is the junction in the main supporting material that integrates 6 with 10 which is the rear segment of the main supporting material that centrally holds the frontal part of the rear cannula in an inflexibly straight longitudinal position. Junction 7 completes the firm support for the outer circular margins of the elasto-valvular component; both 6 and 10 compose the main supporting material joining at 7; 9 is the foremost extension of the axially running bore of rear cannula 13 that communicates with cavity Y of the structure 10, and, such cavity Y frontally bordering at the hind face of the elasto-valvular component; 11 is the unexposed portion of the rear cannula that is held firmly by the central rear part of 10; 12 is the externally threaded screw form adapter which is a rear extension of 10, and which is so constructed to be adaptable with the corresponding internally threaded central bore of the VACUTAINER TUBE HOLDER; 14 is the rear cannular bore; 13 is the exposed hind extension or shaft of the rear cannula; l5 and 16 are both lateral holes of the rear cannula that link bore 14 with the outside; 17 is the point-ending sharply piercing hindmost extension of rear cannula 13.

The main differences between FIGS. 1, 2 and 3 as they respectively represent the first three models of the present invention designated as Models A, B and C, respectively, chiefly rest upon the varying configurations as well as upon either the transparency or the nontransparency of the main supporting material that holds the front and the rear cannulas including the elastovalvular component in place, variations in the shapes of cavities X and Y found therein as far as their respective internal configurations are concerned, and, structural variations relevant to the functional capabilities of the elasto-valvular components.

In FIG. 1, the main supporting material isshown as transparent, and, preferably constructed of strong solid again, preferably made of strong solid plastic material. The advantages of this transparency of the main supporting material are: 1) the allowance of a visual means of checking the functional efficiency of the elastovalvular component situated therein, and 2) the inherent property of the enveloping main supporting material of enabling the operator to gain a positive visual knowledge as to whether or not the optimal blood flow has already ensued from the vein through the bore of the front cannula by watching for the inflow of blood into the cavity X, just before pre-exposing the vacuum of the first collection tube prior to proceeding in the sequence of venous blood multi-sampling.

In FIG. 2, however, the main supporting material may be constructed of non-transparent constitution, which may be of opaque plastic, aluminum or any other preferable metals. This does not favor the provision of a visual indicator means helpful on the part of the operator in affording him the accurate knowledge on the functional status of the elasto-valvular component, nor does it allow him in correctly determining whether or not he has properly punctured the vein before using some of the essential negativity of pressure of the first sample tube. This model, however, is only being introduced as an alternative in case the manufacturer would prefer the production of such non-transparent polysample hypodermic needle for reasons of its own.

In FIG. 4, which is a more magnified longitudinal section in fragmentary form of the middle fundamental components of the Model A of the present invention, the following numerals, letters or letter-numeral combinations are given to the various parts:

The numeral 2 is part of the exposed portion of the front cannula; 3 is the axially running bore of the same cannula; 5 is the rearmost extension of the axially running bore 3; 4 is the unexposed portion of the front cannula that is firmly held in the straight position by 6 which is the front segment of the main supporting material; X is the cavity formed centrally and internally within 6; 18a is the symmetrically and smoothly converging borders of the cavity X; 7a is the junctioning part of 6 and materially joining with the outer sector of 7b which is the foremostjunctioning portion of the rear segment 10 of the main supporting transparent material. Separately drawn between the front and the rear segments of the main supporting material is the elastovalvular mechanism or component shown in the normally closed-lip position. This elasto-valvular component is designated as 8, and, its different parts are represented by the following letters:

d is the outermost part of the said component; a is the flanged portion that fits into the socket built in 7b; e is the flat part that rests snugly against the inner portion of 7a; f is the flat surface at the hind face of the said component that tightly presses against the innermost sector of 7b; b and b are the valvular lips, and, c is the valvular slit.

Y is the rear cavity formed centrally and internally within the structure of the rear segment 10 of the main supporting material; 18b is the symmetrically and smoothly converging borders of cavity Y that ends rearwardly at 9 which is the foremost extension of the axially running bore 14 of the rear cannula; 11 is the unexposed part of the rear cannula that is held firmly and straightly by the central rear sector of the rear segment 10 of the main supporting material; 12 is part of the rear segment 10 which is an externally threaded screw form adapter.

In FIG. 5 which is another more magnified longitudinal section in fragmentary form of Model C of the same invention, the middle features are brought into a more detailed attention, viewing how the different parts are structurally and functionally inter-related to one another from the standpoint of fittable pre-fabricated components on one hand and in the light of a more practical and economical method for mass production.

The following numerals, letters and numeral-letter combination are given to various parts: 2 is the exposed portion or shaft of the front cannula as seen partly in fragmentary form; 6b is the flanged foremost sector of the front segment of the main supporting material,

while 6a is the inner unflanged portion of the same; 7a is part of a circumferentially molded recess at the rearmost outer sector of the front segment of the main supporting material wherein the flanged part of the elastovalvular component, designated in the drawing as letter a, is to be snugly fitted; d is the outermost part of the said component that is to be tightly pressed against the outermost borders of the circularly running recess 7b of the rear segment 10 of the main supporting material; f is that part of the said elastovalvular component that must rest against the rearmost borders of 6a; b and b are both elasto-valvular lips, and, c is the elastovalvular slit. Meticulous observation would reveal that, in the construction of this particular Model C, the fittings of the flanged portion of the elasto-valvular component is reversed in so far as its being compared to the fittings of the same flanged portion seen in Models A and B. This, as can be noticed, is just another structural alternative designed towards achieving another desirable economical aspect for reliable mass-manufacture, however, the chief function of the elasto-valvular component relevant to the valvular lips rearward swing with the aim of attaining the open position, is still focussed towards cavity Y which is the centrally located internal pre-molded cavitation of 10; X is the tubular fore cavity that runs longitudinally and symmetrically within the borders of 180 found at the central part of the front segment 6a of the main supporting material, and that the said cavity X is axially aligned and in direct communication with the rearmost extent of the front cannular bore represented as 3; 18b is the smoothly converging internal physical limitations of the rear segment 10; 9 is the foremost extent of the rear cannular bore 14, and which is in direct space-continuum with cavity Y; 11 is the frontal portion of the rear cannula that is held firmly and straightly in an axial way by the hind central part of the rear segment 10; 12 is a portion of the externally threaded screw form adapter found at the hindmost portion of 10. It is suggested that in this particular model as well as in the other models of the present invention, the best practical way of achieving more effective mass-production calls for the pre-fabrication of the various desired applicable configurations of each important component such as (1) the elasto-valvular component, (2) the front segment of the main supporting material 6a and 6b, wherein the cavity X and the recess 7a are pre-molded, (3) the front cannula mounted firmly in the correct longitudinal position, (4) the rear segment of the main supporting material 10 wherein the cavity Y and recess 7b and the externally threaded screw form adapter designated as 12, are pre-molded,

() the rear cannula fixed in proper position. After the accomplishment of the said pre-fabricated components, the two segments of the main supporting material can now be fused together, sandwiching the grippable parts of the elasto-valvular component between the said front and rear segments. As have been previously illustrated in FIG. 3, wherein the needle is assembled and shown in its entire longitudinal section, the cavities X and Y are separated by the elasto-valvular component only while it is in the close position. The external contour defined by the combination of 6a bordered by the rear part of 6b and the foremost extent of 10 can be very well utilized as the finger-grippable part, such part rendering a convenient shape during the quick installation and subsequent disengagement of the polysample hypodermic needle in relation to the internally threaded bore of the plastic VACUTAINER HOLDER through which 12 is made adaptable.

In FIG. 6 which is an enlarged section of the elastovalvular component that had been centrally sliced in a straight sidewise manner, the following letters are used to represent the different elaborate parts of this Type I of elasto-valvular component:

Letters (1, e, a and f are the outer portions of the said component that engage with 7a and 7b of the front and rear segments of the main supporting material which have been previously named and described in FIG. 4. The only differences here are the presence of part g which is merely a flat, hindly situated, broadly running circumferential indentation from the flat surfaces off, and the basic function of this is merely to decrease the material thickness of that part preparatory to the concave abrupt indentation 111 that is of narrow width and, again, circumferentially running when seen from the end-view, and found just before the valvular lips take form within the confines of the hind face of the said elasto-valvular component. The main function of hl is to allow the valvular lips with the easy bending characteristics in their rearward swing during the attainment of the opening phase while the VACUTAINER tube is in the process of aspirating the necessary blood volume from the vein through the poly-sample hypodermic needle. The purpose of the hl cbficavirysmeaavamageous diminution of the rubber material along that area which, in effect, will offer more pliability on the part of the automatically actuatable valvular lips, a necessity in this particularly stiffer constitution of the elast-valvular component to make such actuateable valvular lips much more sensitive to pressure differential gradients. The part 112 is the corresponding cancave abrust indentation opposite hl and located at the fore-face of the elasto-valvular component; h2, likewise is narrow in width, and, located just before the start of the outer formation of the valvular lips, and also running circumferentially when seen from its front view; b2 also adds to the desired pliability of the elasto-valvular lips due to the effects of re-calculated material decrement along its extent resulting in less stress that would otherwise cause greater resistance to the rearward swing of the elasto-valvular component. On the basis of such construction of this particular type, it is clear, from the viewpoint of material thickness, that the valvular lips constitution is thickest near the inner borders of hl and b2, and then gradually diminishing in thickness towards the central part wherein the valvular slit is found. In the elasto-valvular components construction, therefore, it is at point or line defining the extent of c that is structurally least resistant against the hindwardly propelled fluidic mass of blood emanating from the vein, so that, as soon as the vacuum of the VACUTAINER tube is correctly engaged with the rear cannula, the greater aspirating power of the said collection tube will cause a greater pressure differential between the blood-filled cavity X and the cavity Y that is directly in space continuum with the bore of the rear cannula, which is now linked with-the vacuum. This condition triggers the valvular lips to achieve relative optimal apertural sizes in direct proportion to the pressure differential changes; the valvular lips opening activity at the site of the valvular slit 0 brings forth the flow of blood specimen for optimal transport from cavity X to cavity Y and then into the said VACUTAINER tube through bore 14 of the hind cannula.

In FIG. 7, similarly, the different letter designations as given to the elasto-valvular component illustrated in FIG. 4, are basically the same, and that the functions of the different parts are also the same. This illustrates another type of elastovalvular component named as Type II. It is only slightly different from Type I shown in FIG. 6. In this elasto-valvular component, the other parts corresponding to Type I are similar except for the absence of parts g, hl and 112. Of importance to note is that the valvular lips b and b are structurally shaped to show a more forwardly inclined contour in relation to the perpendicular outlines of configurations e and f. Also apparent is the characteristically larger area of elliptical swing of b and b. This design may prove to be favoring the use of a softer structural property of material as an essential factor in the construction of this particular type of elasto-valvular component.

In FIG. 8 which illustrates the Type III of the elastovalvular component, the letter-designated parts a, d and e correspond to the engageable configuration that is made to be adaptable to the pre-fabricated recesses 7a and 7b seen in FIG. 5; the part f is made flat to snugly press against the flattened hindmost border of the front segment of the main supporting material 6a and 6b shown in FIG. 5. From the inner extents of part e and f of the component, a pair of right-angled fore and hind indentations opposite each other start the structural configurations that finally form the valvular lips b and b; j and j are the sites where the hind face of the valvular lips b and b begin to bulge in material thickness to form i and i which are actually thickened edges of the elasto-valvular lips, and which form a streamlined circularly running bulge across which the valvular slit or slits are made. The chief rationale governing the pre-forming of this structural thickening i and i is the provision of more material constitution around the edges of the valvular lips, aimed towards the attainment of steadier and more resistive elastovalvular edges such as in the case wherein the rubber material selected for construction is in the order of a softer or of a more physical yieldable consistency char acterized by: (l) lesser density rubber material with the least stiffening additive ingredient, or (2) rubber material of optimal structural quantities of spongy or tightly foamed nature. Note the reversed installation of the flanged outer portion defined by the a, d and e configuration of the elasto-valvular component which can be adaptable to the pre-recessed parts 7a and 7b of the front and rear segments of the main supporting material shown in FIG. 5, in contrast to the rear-facing installation of the respectively flanged portion of the elasto-valvular component of the Type I or Type II seen as adaptable to the corresponding recess 7b of the rear segment 10 of the main supporting material as illustrated in FIG. 4. However, the rearward swing of the valvular lips b and b in order to achieve an open position as a result of the valvular-lips automatically actuated response to the sucking action by the vacuum of the pre-evacuated sample tube, remains comparatively the same as in Types I and II of the elasto-valvular component.

In FIG. 9 which is an enlarged end view of the Type I of the elasto-valvular component, the portion occupied by part a, which is seen in the side sectional view in FIG. 6, is illustrated clearly as extending around the outermost margin of the component, and, that which runs circularly and flatly. Parts f and g, respectively are shown occupying the next two inner portion of the same component, both partsf and g, likewise, running circularly, flatly; 121 which is the hindly situated circularly running narrow groove is illustrated bordering the outermost extensions of the valvular slits c1, c2 and 03 that form the corresponding valvular lips b1, b2 and b3.

In FIG. 10 which is the enlarged end view of the Type II of the elasto-valvular component, vividly shows the circularly and flatly running contours defined by parts a and f, and that b continues, materially, towards the center and actually forming the four symmetrically arranged valvular lips bl, b3, b3, and b4 after the valvular slits c1 and c2 criss-cross straightly across the center, each slit dimension being equal and starting the physical break equi-distantly from the inner border off, and just a few measure centrally within the confines of b.

In FIG. 11 which is the enlarged front view of the Type III of the elasto-valvular component, the flatly and circularly running areas of parts a and fcan be seen; within the scope ofb can be observed the equally dimensioned valvular slits cl, c2, and 03 which confluence and cross the center up to their correspondingly opposite limits in relation to their respective starting points. The resultant ofthis slitting method is the actual formation of the equi-angular shapes of the respective valvular lips b1, b2, b3, b4, b5 and b6.

Specially important to note is that, in FIGS. 6, 7, 8, 9, and 11, the elasto-valvular lips that correspond to each of the three different types of elasto-valvular components, are all in the normally closed position.

FIG. 12 which is the enlarged pictorial representation of the relationship between the vein, the blood, the polysample hypodermic needle and the VACU- TAINER HOLDER as drawn inter-connectedly in the central longitudinal section, vividly illustrates the following labeled parts:

The numeral 1 is the forward beveled sector of the front cannula 2, and, which is presently shown having made the optimal penetration of the venous wall 19 at point 21, and that, part of the blood flowing through the vessels lumen is transported through the bore of the front cannula and filling the cavity X formed within the confines of 6', 8 is the elasto-valvular component; the cavity Y which is formed within the confines of 10 is shown still unoccupied by blood; 12 is the externally threaded screw form adapter of the poly-sample hypodermic needle that has been firmly positioned by 22 which is the foremost central structural enlargement of the VACUTAINER HOLDER, such structural enlargement having a central internally threaded bore, preformed to fit l2; lateral holes 15 and 16 of the rear cannula are shown located near the point-ending piercer 17 of the rear cannula; 24 is the section of the tubular body of the plastic VACUTAINER HOLDER, and 23 is the barrel within its internal confines; 25 is the flanged portion of the plastic VACUTAINER HOLDER that is finger-grippable and utilized by the operator during the blooddrawing procedure.

The blood flow from the vein into the said cavity X has been brought about because of the existing pressure differential between the venous side and the lesser pressure inside cavity X. Whatever volume of air previously occupying the said cavity is of considerably negligible quantity, for in the actual scale of cavity X, the space is only of a small dimension, enough to accommodate just a minute amount of blood ensuing into it from the venous side through the bore of the front cannula; such small blood quantity perceivable by the operator due to the transparency of the enveloping plastic material of the front segment of the main supporting material, thus indicating positively whether or not the proper venous penetration has been made before exposing the vacuum of the initial pre-evacuated sample tube. This small quantity of air normally trapped inside such cavity X of a pre-used poly-sample hypodermic needle would, in no way, endanger the patient with a substantial air emboli, for such gaseous mixture would be prevented from entering the vein due to the preexisting pressure differential between the greater venous pressure and the lesser pressure characteristic of cavity X when the front cannula has made the proper venous penetration. Instead, blood is transported from the venous side through the front cannula bore and into the said cavity X, displacing the previously occupying small amount of air, such blood inflow forcing such thin gaseous mixture through the very narrow but adjustable valvular slits of the elasto-valvular component capable of making the essentially selective gaseous escape from cavity X into cavity Y. As the air from cavity X enters cavity Y, a correspondingly equal volume of air escapes through the rear cannular bore, exiting from the lateral holes 15 and 16 to the ambient environment. The blood being of much denser and viscous property cannot escape the very narrow valvular slit or slits, in contrast with the positive escaping ability of the much lesser density air. In this situation, the valve cannot be actuated to widen considerably in aperture size so as to permit the characteristic viscous-quality transport of blood due to the biophysically based reason that the pressure differential between the venous side and the ambient condition is inhibited by the pre-calculated structural stiffness of the selected construction of the elasto-valvular mechanism. Hence, no blood would be coming outfrom the rear cannula, even though the correct puncture of the vein has already been made, for the initial VACUTAINER tube is still unlinked with the needle. At this phase of the operation, the elastovalvular mechanism cannot achieve the open position in conjunction with the actual process of venous blood extraction, since the negativity of pressure of the vacuum of the said sample tube has not yet been connected with the bore of the rear cannula that would have caused the valve to open allowing blood transport from cavity X into cavity Y then through the rear cannular bore.

Included in FIG. 12 is the said first or initial VACU- TAINER tube that is still unconnected to the hind portion of the rear cannula; such container tube is viewed in the side elevation and shown partly inserted into the barrel of the holder 24. Numeral 26 is the flanged rubber stopper of the VACUTAINER tube 27, and that, the rubber stopper has not yet been pierced by 17, thereby, the vacuum contained inside the said container tube is still unexposed. The said tube in this case, as can be seen, is yet devoid of any blood contents.

FIG. 13 is a much more magnified pictorial illustration of the relationship referred to in FIG. 2, except that the VACUTAINER tube is ommitted in the drawing. The blood 20 is shown flowing from the vein l9, and partially transmitted through the bore 3 of the front cannula 2, having passed through the front cannulas rear exit 5 to fill cavity X. As can be clearly understood, the blood has been transported from the venous lumen because the foremost open beveled end of the front cannula has made an optimal penetration of venous wall 19 at site 21, and that, the said beveled portion is properly positioned inside the vein. Therefore, as previously mentioned, the blood is made to pass through the said bore 3 into X because of the existing substantial pressure differential between the venous side and the cavity X, however, due to the precalculated stiffness of the elasto-valvular component enabling it to resist the range of possible venous pressure fluctuations from individual to individual, there can be no blood volume transfer from cavity X to cavity Y until the pressure differential becomes greater as can be achieved when the VACUTAINER tube has already been installed at the opposite side. Notice that, by looking at the unwidened view of the valvular slit 0, and, noticing the unswung valvular lips b and b, the elasto-valvular mechanism is still substantially in the normally close position. The numeral 7 represents the junction line between the front and the rear segments 6 and 10 of the main supporting material. At this particular phase of operation, since the first container tube has not yet been installed, cavity Y is yet devoid of blood contents. And, due to the transparency of the 'main supporting materials front segment, the blood inside cavity X can be seen by the operator, thereby indicating to him when the vein had already been properly punctured and the initial blood flow from the vein through bore 3 had already ensued. The operator can, at this time decide to link the vacuum of the said container tube into the system without any trial-and-error method. By following this procedure, utilizing the advantageous feature of the transparency of the said device, the vacuum capacity of the pre-evacuated sample tube cannot be prematurely exposed. The numeral 9 is the rear cannular entrance that communicates cavity Y through bore 14 to the ambient environment when the poly-sample hypodermic needle is not linked with the tube or, to the vacuum of the container tube when the said poly-sample hypodermic needle is connected with the said pre-evacuated vial. The parts and functions represented by the numerals 12, 22, l5, l6, l7 and 24 have already been previously mentioned in FIG. 12.

In FIG. 14 which is another enlarged pictorial illustration showing the relationship between the interconnec'ted important components included in the VACU- TAINER METHOD of blood specimen extraction vividly illustrates the propagation of blood flow through the now open elasto-valvular component, after the VACUTAINER tube has been installed with the system. The causative factor for the opening of the valvur lar component 8, causing blood transport across its opened valve, from cavity X into cavity Y, and, propgated through the bore of the rear cannula into the aspirating sample tube, after exiting through the lateral holes 15 and 16, is the creation of the automatically actuating greater pressure differential that now exists between the positive pressure inherent in the venous side, and the negative pressure characteristic of the vacuum contained within the evacuated collecting vial on the other side. This abrupt increment of the said pressure differential as a result on the installation of the said tube, triggering the valvular lips to swing rearwards, permitted the widening of the valvular slits, thus allowing blood to flow through the entire device. The arrows r1 and r2 indicate the direction of the blood quantities being aspirated from lateral holes 15 and 16, respectively, during the collection of specimen into the said VACUTAINER tube. Part 26a is the flanged portion of the rubber stopper plugging the container tube, and, 26b is the diaphragm of the same rubber stopper that has now been pierced by the point-ending piercer of the rear cannula. All the other parts represented by the other numerals in this figure have been previously named and described in FIG. 12.

FIG. 15 which is another enlarged pictorial representation, drawn partly in central longitudinal section, includes the relationship between the aforementioned important components, but, this time, the VACU- TAINER tube filled with collected blood specimen, is shown to have been disengaged or pulled away from its physical connection with the poly-sample hypodermic needle. It is of utmost importance to note that, due to the inherent elasticity of the elasto-valvular mechanism 8, the corresponding valvular lips had sprung back to their original close position as an after-effect of the tubes having been pulled away from its cannular linkage. The pressure differential that now exists between the venous side and the ambient environment on the other side is precalculatedly too weak to maintain the valves open position; the elasto-valvular component having been specially constructed and pre-tested to attain the specifically desired safe range of resistive elasticity prevents the propagation of the continuous blood flow through the valve when no VACUTAINER tube is interconnected with the system. In this figure, the front cannula is still in direct communication with the vein, and through blood is now present in both cavities X and Y as well as inside the front and rear cannular bores, blood drip or spatter into the ambient environment is prevented from occurring, for the reason that no further blood flow is permitted by the close valve to cross through it at this time. All the numerals and letters that represent the specific parts and functions were already described in FIGS. 12, 13 and 14, with the exception of numeral 20 which represents the blood that had been collected and shown as contained inside the VACUTAINER tube.

After the first blood-filled collection tube had been removed from the plastic VACUTAINER HOLDER, the next pre-evacuated sample tube shown in FIG. 16 can now be installed into the barrel of the said holder, and then, connected again with the same system by forwardly pushing the tube 27 at its base with the thumb or palm of the hand, so that the rubber stopper can be properly pierced at its diagphragmatic area by the pointed sector of the rear cannula. Since there is no external rubber sleeve at this rear cannula as in the case of the B-D MULTIPLE-SAMPLE I-IYPODERMIC NEEDLE, the piercing of the rubber stopper by the rear cannula of this presently applied for invention can be performed more easily on account of the advantageous property of the device in affording greater ease in the operators performance while offering a much less pre-disposition to traumatic injuries on the part of the patient. As soon as the second VACUTAINER tube has been installed, the blood flow would again ensue, for the valve will regain its automatic opening phase as a result of the triggering effect of the sudden pressure differential increment between the venous side and the aspirating vacuum of the collection tub, thereby causing blood to be collected into the second sample tube.

During the filling phase, the valves aperture is not constant because the valvular opening and closing responses are relative to the pressure differential gradients between the venous side and the degree of negativity of pressure of the collection tube. Hence, at the start of the aspiration phase effected by the vacuum, the valvular lips are readily swung rearwards from their close position, towards the direction of the aspirating medium, widening to the largest attainable aperture size depending upon the intensity of the vacuum, which, of course, would also depend upon the diameter and length of the VACUTAINER tube used. As the fluidic mass of whole blood is being collected, the vacuum capacity correspondingly decreases, and, the valvular lips automatically respond by relatively narrowing the aperture sizes up to a point when it is about closed, at which time, most of the vacuum has already been consumed due of the positive occupancy of the collected blood specimen therein. From the standpoint of Biophysics, this adjustability of the valvular aperture sizes effected by the responsive automatic adaptibility of the said valve to the variations in the pressure differential gradients, in addiiton to the structural streamlining of the valvular lips themselves, jointly help reduce the danger of disintegration of the cells suspended in the plasma. This is one of the chief advantages of this polysample hypodermic needle over those in current use that are inefficient in adjusting to such pressure differential gradients secondary to the constant aperture size through which the blood sample is forced to pass. The high shear forces affecting the onrushing whole blood being collected through the currently produced hypodermic needles, for example, those produced by 8-D and MPL, are not substantially reduced hence resulting in a greater chance of hemolysis and other cellular disintegration.

After the second collection tube had been filled with specimen, the cycle of operation is repeated as aformentioned, soon as the third sample tube has been installed.

In case the operator desires to disengage the collection tube away from its linkage with the poly-sample hypodermic needle, before the said pre-evacuated sample tube has completely been filled with specimen, the basic design of the inter-paced lateral holes and 16 may prove as an essential deactuating means which can optimally cause the easy snapping of the valvular lips towards the close position. This advantage is brought about because the two inter-paced lateral holes become sequentially blocked by the solid mass of rubber that constitutes the pierced disphragm of such rubber stopper during the slow pulling of the sample tube away from its connection with the rear cannula. Note that the inter-pacing of the lateral holes does not have to be exactly in the same proportion as illustrated; such interpacing of the lateral holes can be made farther apart as far as the longitudinal relationship to one another is concerned provided that better efficiency of the device is achieved. The easy, yet quick enough closure of the said valve as the operator gently pulls away such sample tube will prevent the occurrence of blood drip during the span of time between inter-tubular changing in the course of multi-sampling from the vein.

In FIG. 18 which is the enlarged end view of the elasto-valvular component of the Type I, it is fully illustrated how the valvular lips attain their completely open position at the height of the vacuums aspirating power. This fully open position of the valve is achieved at the time when the pressure differential between the venous side and the said vacuum is at the greatest value. As can be seen, the valvular lips appear to have reacted in such an orderly manner due to the presence of the pre-set equal length and equi-angularly arranged valvular slits c1, c2 and c3, which are originally illustrated in the closed position in FIG. 9. This allows the corresponding valvular lips the freedom of displacement reactivity that can variably achieve the adjustable aperture sizes relative to the aforementioned pressure differential gradients.

The parts a, f and hl correspond to the parts already named in FIG. 9, and can be seen almost identically except for the following (1) The valvular lips are swung rearwards thus attaining the open position (2) hl is seen to be more narrowed secondary to the compressing action of the rearward swing of the valvular lips b1, b2 and b3 (3) The presence of 10 which is a crosssection of the transparent plastic solid material that supports and envelopes the elasto-valvular component (4) The presence of :1, t2, t3 and t4 seen as equidistantly placed inverted V-shaped protrusions at the outer edge of 10; the purpose of such protrusions being to provide an adequate structural means to increase traction or finger-grippability so necessary for the effective installation and subsequent disengagement of the adaptable end of the poly-sample hypodermic needle to the respective internally threaded bore of the VACUTAINER HOLDER.

In FIG. 19 is the enlarged end-view of the Type II of the elasto-valvular component as it appears being enveloped around its outermost circumference by the cross-section of the transparent solid plastic material 10. The valve is shown in the fully open position after it has abeen automatically actuated to open by the pressure differential between the venous side and the vacuums negativity of pressure. The valvular lips b1, b2, b3 and b4 had been swung rearwards by the aspirating action of the said vacuum. It is through this open valve that the blood is made to pass from the venous side into the VACUTAINER side. The parts a and f of the elasto-valvular component are shown to be running circularly and flatly as in FIG. 10. The valvular slits cl and 02 are well widened, and only the outermost borders of the said slits can be seen in the drawing. The exterior of the enveloping plastic material 10 that firmly holds the elasto-valvular component in proper place can be observed to have fingergrippable arc-like edges, again, for the purpose mentioned similarly in the discussions involved in FIG. 18. The said traction edges are represented by the letter t.

FIG. 20 is an enlarged frontal view of the elastovalvular component of the Type III as shown in FIG. 11, but this time, the valve is in the open position; the valvular lips having been swung rearwards cannot be fully sen. Only the outlines of internal bases of the valvular lips bl, b2, b3, b4, b and b6 are seen as they are viewed frontally; inter-paced between the bases of the six valvular lips are the outermost borders of the widened valvular slits cl, c2 and c3; parts a and f are seen running circularly and flatly which are similarly shown in the same fashion in FIG. 11.

From this viewpoint, it can be visualized how the blood is smoothly transported from the venous side through the streamlined aperture into the aspirating side of the system, after intercommunication between cavities X and Y has been established soon after the valve opens.

In FIG. 21 which is the enlarged central longitudinal section of Model D of the present invention the numerals 1, 2, 3, 4 and 5 that represent the different parts of the front cannula, are of the same names and functions as those similar numerals in the previously discussed models of this currently applied for poly-sample hypodermic needle. The same is true with the parts represented by the numerals 11, 9, l3, and 14 which are different parts of the rear cannula, with the exception of numeral 29 which represents the hindmost beveled sector of the rear cannula, the part that does not appear the same compared to that rear cannular part in Models A, B and C because, here, 29 is of a beveled-end configuration with an axially situated exit or cannular hole through which blood can pass into the aspirating pre-evacuated sample tube. Pertaining to 6 and 10 which represent the front and the rear segments of the main supporting material, respectively, the essential difference is a matter of configuration internally, as far as the shapes of cavities X and Y, and, externally, as far as the countours of the exterior.

Again, the elasto-valvular mechanism or component is situated between the front and the rear segments of the main supporting materials as indicated by the central cross-section of the said mechanism shown to be sandwiched between 6 and 10. The borders of the said elasto-valvular component are firmly placed in position permitting the normally close elasto-valvular lips bl and b2, to separate cavity X from cavity Y and also allowing the optimal freedom of such eIasto-valvular lips in responding to the relevant pressure differential sensitivity range.

The numeral 40 is a streamlined internal contour of the rear segment of the main supporting material, and, as is evident, the purpose is to allow a pre-calculated space for the accommodation of the allowable limits of the rearward swing of the elasto-valvular lips during the opening phase of the valve.

Numeral 7 is the junction between the front and the rear segments of the main supporting material, and, at this site, the perpendicular lines 30 and 30 are drawn straightly; the rearwardly pointing arrows m and m, and the forwardly pointing arrows p and p are indicated in relation to whatever particular view is taken with respect to lines 30 and 30 of FIG. 21. I

Perpendicular lines 32 and 32 are drawn and seen touching the front segment 6 of the main supporting material, and, arrows q and q are illustrated as rearward-pointing.

Perpendicular lines 34 and 34 are shown touching the rear segment 10 of the main supporting material, and, the forwardly pointing arrows s and s are illustrated relating to the forward view with respect to lines 34 and 34.

Each pair of perpendicular lines such as 30 and 30, 32 and 32, 34 and 34, as well as each pair of arrows m and m, p and p, q and q, s and s, are correspondingly illustrated in the respective drawings called for in the differing point of views such as in FIGS. 23, 24, 25, 26, and 27.

The numeral 12 is the externally threaded screw form adapter which appears similar to that same part in all the previously illustrated models.

FIG. 22 is a more magnified central longitudinal sectional view, partly in fragmentary form of the model D of the present invention in so far as its relationship with the other pertinent items or factors of the VACU- TAINER SYSTEM are concerned as applied during the actual process of blood drawing. The numeral 20 represents a blood quantity shown flowing and originating from the vein, and, hereby illustrated to have been transported through the cannular bore 3 of the front cannula 2, after the forward beveled end 1 has correctly punctured one side of the venous wall 19 at site 21; and that blood 20 having already entered cavity X after exiting from 5, and, having passed through the open valve of the elasto-valvular component 8, and then propagated in its flow through cavity Y as well as through cannular bore 14 and into the interior of the installed fragmentarily drawn VACUTAINER tube, after having exited axially from the end of the rear cannula 13 in the direction of arrow r.

According to the same principle of operations involved in the features of the present invention, the elasto-valvular mechanism responds to the pressure differential gradients existing betwen the venous side and the VACUTAINER side, by means of opening its valvular lips to allow the passage of blood through the device. This is due to the pre-calculated functional reactivity of the actuatable structural designs as well as density, elasticity, resistance, configuration streamlining and thickness of the elasto-valvular mechanism.

Also shown in the drawing, 6a is an external enlargement of the front segment 6 of the main supporting material, and, that 6a had been constructed for the purpose of allowing the necessary material support so as to enable the lengthwise extent of the elasto-valvular component of this Type IV to be properly and symmetrically enclosed, and, firmly sandwiched in place between the front and the rear segments of the main supporting material.

Also included in the drawing is the frontal part of the VACUTAINER HOLDER 24, made of rigid plastic, and, having accommodated the fragmentarily illustrated sample tube 27, within the tubular confines of the holders bore 23. The rubber stopper plugging the sample tubes entrant end has been completely pierced by the rear cannula 13 at the site of the rubber stoppers diagphragm 26b shown to be centrally thinner in structural dimension.

The flanged part 26a of the rubber stopper is shown to be thicker in sectional construction.

The entire poly-sample hypodermic-needle is-firmlyinterconnected with, the plastic VACUTAI-N ER I-IOLDER and this has been echieved bythe correct fitting afforded by 22 which is' the central external enlargement of the holder; 22 having an internally threaded bore through which the externally threaded screw form adapter 12 of the poly-sample hypodermic needle suitably and firmly fits.

In FIG. 23 which is the enlarged cross-sectional view of the poly-sample hypodermic needle taken from lines 30 and 30 and seen in the direction of arrows p and p, the entire hind-face view of the elasto-valvular mechanism or component represented by numeral 8 of the Type IV known as the Dual-Lip Polygonal Elasto- Valve, is properly illustrated, and the outer lengthwise margins of the said component are shown to be flatly secured against the correspondingly flat depression that conforms with the polygonal shape and dimension of the said component; such depression being located centrally and at the rearmost end of 6a as well as that of part 6. The hind-face of the said elasto-valvular component is basically flattened except at the edges of wherein the structure had been contoured inwardly and slightly of convex nature. The valvular slit 0 is only a singular straight slit or incision across the middle part of the said component, and that which runs at right angles relative to the perpendicular symmetrically arranged equally dimensioned incisions jl and j2 that are situated correspondingly to each lateral region of the said component. The eIasto-valvular component 8, having an I-I-shaped inter-connected incision-complex as defined by the combination of valvular slit 0 and the laterally located incisions jl and j2, is illustrated in the normally closed position. The left and the right lateral margins kl and k2 are material continuities of the said component for definite manufacturing advantage, namely, to be able to form the said component into a singular piece without altering the proposed basic functional feature of the l-I-shaped incision-complex. The circular dotted lines, bisected by valvular slits C, and, labeled as X is actually the unscaled representation of the circular borders of cavity X of the front segment of the main supporting material; said circular borders that axially ends at the fore-face of the elasto-valvular component cannot be seen when the valve is in the closed position as indicated by the appearance of the unswung valvular lips b1 and b2. Shown to be enveloping the entire polygonal borders of the elasto-valvular component is the transparent cross-section of the oval-shaped enlargement 6a; the ovality of the said enlargement can be very well utilized in providing an excellent finger-grippability necessary for the fast installation and easy disengagement of the poly-sample hypodermic needle to and from the respective inter-linking part of the plastic VACUTAINERl-IOLDER.

In FIG. 24 which is an enlarged cross-section of the same poly-sample hypodermic needle, also taken from lines 30 and 30 and along the direction of arrows p and p of FIG. 21, the same hind-face view of the Type IV Dual-Lip Polygonal Elasto-Valve seen in FIG. 23, is vividly shown, but, this time, the valve itself is illustrated in the open position. It can be observed by the clarified definitions of the shadings in this particular drawing that the valvular lips [11 and b2 have been flipped rearwardly so that the valvular slit c which has been clearly visualized in FIG. 23, but, having now completely widened, cannot be seen as a slit, but instead, as a wide space that centrally exposes the most part of the end-view of cavity X. During this phase, blood is transported from cavity X into cavity Y because of the opening of the dual-lip elasto-valve. The

rearward swing of the elasto-valvular lips b1 and 122 has physically been made possible due to the incisions jl and j2 that run along the sides of the valve; and that 1 and 2 are just shadings of the linearly illustrated bending of the hind face of the flat rubber material as a result of the rearward swing of the valvular lips b1 and b2, respectively. There is no change in appearance in the cross-section of as far as its enveloping and supporting the entire flatly positioned elasto-valvular component as compared to FIG. 23, however, since the valve is now in the open position, the central part of 6a is seen surrounding the circular borders of cavity X. There is no alteration in appearance of k1 and k2 since these margins are the physical continuities of the rubber material that remain unaffected by the opening and closing of the valvular lips, and, this is due to the presence of incisions jl and j2 that disengage the said margins kl and k2, respectively, from the motional reactivity of the valvular lips bl and b2.

In FIG. 25 which is the enlarged cross-sectional view of the poly-sample hypodermic needle, taken from lines 30 and 30, but, this time along the direction of arrows m and m as seen in FIG. 21, the elasto-valvular mechanism cannot be visualized. The cross-section of cavity Y is shown to be centrally located, and around it is 40 which is a marginal circularly running-convexly contouring structure that opens innerly into Y and wedges outerly with the flat foremost central circular borders of 6a of the rear segment 10 of the main supporting material. The use of 40 permits a precalculated space allowing the optimal rearward swing of the valvular lips, and therefore, since the elastovalvular components fore-face is actually the one that completely covers the rearmost extent of cavity X, the elasto-valvular components hind-face does not necessarily have to cover the entire extent of 40 to prevent the blood from leaking into cavity Y from cavity X when the valve is in the closed position.

In FIG. 26 which is the enlarged cross-sectional view taken from lines 32 and 32 along the direction of arrows q and q as seen in FIG. 21, the circular borders of front segment 6 of the main supporting material are seen externally and internally. Inside the cross-section of the said transparent structure 6, the central area occupied by cavity X is clearly shown.

In FIG. 27 which is the enlarged cross-sectional view takne from line 34 and 34 along the direction of arrows s and s as seen in FIG. 21, the circular borders of the transparent-structured rear segment 10 of the main supporting material are seen exteriorly and interiorly. Inside this structure, the central area defining cavity Y is vividly illustrated.

In FIG. 28 which is an enlarged central longitudinal view in sectional and in partly fragmentary form of yet another alternative version assigned here as the Model E or called the Euclidean Automatic Uni-Lipped Elasto-Valvular Poly-Sample I-Iypodermic Needle, the

- automatically-actuateable valve named as the Uni-Lip 'els of this same invention, in that, the. valve would at- 25 tain the open position in gradations of rearward swing depending upon the pressure differential between the venous side and the aspirating vacuum at the VACU- TAINER side. As the negativity of pressure of the preevacuated sample tube is consumed as a result of the increasing quantity of blood specimen collected therein, the valve gradually closes secondary to its inherent structural elasticity. When the said tube is removed from its connection with the said device, the

blood from cavity X is prevented from being transported into cavity Y due to the optimal pre-calculated stiffness of the structural makeup of the said valve, considerably resisting a rearward swing because the pressure differential between the highest venous pressure and the existing ambient pressure would prove to be still weak enough to actuate any substantial degree of valvular rearward swing. This is how blood is inhibited from dripping during the process of multiple-sampling, while the hypodermic needle is still connected intravenously. The main difference of this valve as compared to the other valve-types mentioned before is that there is no slit found here, this valve capable of reacting to the pressure changes as a singular-lip structure. Again, preferably, there are two segments of the main supporting material-the front segment 6 and the rear segment 10. Both segments are joined together at site 7, and, sandwiched between the said two segments is the upper portion of the elastovalvular component that is held firmly in place, while the lower portion of such elastovalvular mechanism is free to move rearwardly and back to its original close position. In the close position, the botton portion of the component optimally rests upon a groove formed at the medial part of the joint structure of the two segments of the main supporting material. This internally located groove furnishes a suitable configuration to permit the corresponding contour of the said bottom portion of the said elastovalvular component so as to be able to physically separate cavities X and Y from each other when such valve is in the completely close position. There is also provided a two-unit stationary or immovable cannulas-the front cannula and the rear cannula designated by the numerals 2 and 13, respectively, fixed in firm longitudinally aligned fashion by the corresponding structural parts of the front and the rear segments of the main supporting material. The front cannula has a foremost beveled edge 1 which is utilizable for the puncturing of the blood vessel wall and other tissues superficially situated in relation to the said blood vessels wall; such cannula being provided with a longitudinally running bore 3 exiting at 5 into the cavity X. The rear cannula has a point-ending piercer 17 which is utilizable for the easy puncturing of the diaphragm of the rubber stopper of the VACUTAINER tube. A leteral hole is provided and which communicates cavity Y with the vacuum of the VACUTAINER tube through nono-oval 8 op, which is illustrated as it can be visualized in the open position whereby the valve has been caused to be dislodged from its originally closed, plugging position represented by the area 8cp bordered by the broken line curvature. The valve is centrally found and supported by a pair of elastic connectors 8es on each lateral part, and that such connectors linking the ball-like valve with the correspondingly firm gripping portions within the internal structure of the main supporting material. The structural makeup of the monooval valve should preferably be of light-weight less dense rubber material having pre-calculated or pretested capability of optimally responding to the required sensitivity values of pressure differentials governing the chief principles of operations of this invention. The elastic connectors 8es are also pre-tested in their elasticity range so as to be capable of allowing the dislodgment and engagement of the ball-like valve relative to the changes of pressures. In the closed position, the blood cannot enter from cavity X to cavity Y, but, in the open position the blood can be transported from the venous side into the properly attached preevacuated sample tube. All the other numerals represent the same parts as in FIG. 28 except the addition of another lateral hole 16 situated just opposite lateral hole 15; both lateral holes are aimed for the establishment of communication between the cavity Y and the aspirating vacuum of the said sample tube. Notice the longer length of both the lateral holes 15 and 16 for the purpose of creating an instantly greater sucking action when the rear cannula has established communication with the vacuum of the collection tube; such greater equi-aspirating action of the dimensionally equal and non-inter-paced oppositely placed lateral holes would cause a balanced dynamically favorable displacement of the ball-like valve without considerable linear deviation of the said valve in relation to the centrally situated rearmost extent of cavity X, and, at the same, preventing any possible vibrational flutter of the dislodged balllike valve that could interrupt the optimally smooth flow of specimen across the valve during the whole blodds passage along such open medium.

In the embodiments illustrated in the drawings, it is to be understood that such drawings are for the purpose of merely visually describing the six preferable models including the different elasto-valvular types for the design of this new polysample hypodermic needle, hence, the said drawings have not been drawn in the exact scale and proportion as far as each part interrelates with the other parts. As can be observed, the configurations, both exteriorly and interiorly, vary depending upon the selected model as well as the chosen elasto-valvular type, it is also possible that certain other adjustments in measurements and other forms of structural modifications can also be made aimed to suit the optimal level of functional capabilities that well characterize' the best advantages for the device as determinable in the course of experimental pre-testing of the various parts comprising such device. The inventor, therefore, does not limit the scope of his applied for invention to the exact structures described and shown here as long as the novel features embracing the applicable principles of his invention in this particular field of blood-sampling from the vein using pre-evacuated sample tu-bes arepreserved. In morespecific terms, some modifications may be made on the following:

a. the shapes and sizes of the cavities X and Y; 

1. In combination, a blood specimen collection assembly comprising a hallow hub means, a resilient valve, a first hollow cannula and a second hollow cannula, both of said cannulas fixed axially in relation to each other as well as in relation to the center of the said valve by the said hub means, and wherein the first said cannula having a pointed end being for the purpose of puncturing the skin and the blood vessel wall, and wherein the said second cannula having a pointed end being for the purpose of piercing the rubber stopper of the evacuated specimen collection receptacle to establish communication between the said assembly and the vacuum of the said evacuated specimen collection receptacle, a first cavity and a second cavity, both of the said cavities located interiorly of the said hub means, said hollow first cannula communicating with the said first cavity providing a fluid inlet, and, said second cannula being also hollow and communicating with the said second cavity providing a fluid outlet, said valve situated therebetween the said first and second cavities, said valve having a cross-section that is thickest at the outward portion and thinner at the inward portion and particularly thinnest at the central part making the said valve structurally sensitive to the relevant pressure differential changes focussed at and immediately around the said central part of the said valve, said valve in cross-section describing an inclined arc-like convexity toward the first cavity at its foreface proximal to the said first cavity, and, said valve defining an inclined arc-like concavity toward said second cavity at its hind-face proximal to the said rear cavity, the combination of both the said inclined arc-like convexity and concavity being formed from the outer section of the said valve toward the said valve''s central part with a taper of the said valve toward the said valve''s center, said valve provided with a plurality of cuts across its central part and said cuts converging toward and intersecting the said valve'' s center defining a plurality of said cross sections; said valve held in stationary position at its outer border by the inner portion of the said hub means; said valve normally in the closed position when the said assembly is not properly engaged with a potent evacuated specimen collection receptacle and not properly linked with an active vein; said valve being in a minutely semi-open position as far as air transit from the said first cavity to the said aft cavity is concerned when the said first cannula is in communication with the kinetically flowing venous blood running through the venous lumen of the properly penetrated vein thus allowing blood transport from the venous side into the said fore cavity, but, said valve, after air transit across its minutely widened cuts not permitting the viscous blood to transfer across said valve into the said second cavity and into the said evacutated receptacle until a substantially potent aspirating force triggers the said valve to the actually open position so as to allow the blood specimen collection through the said assembly into the said aspirating receptacle, said valve in the open position achieving gradual variation in aperture sizes directly proportional to the degree of pressure difference between the venous pressure and the aspirating negative pressure of the said communicated evacuated specimen collection receptacle so that in effect the said valve serves as a compensatory shock absorber automatically decreasing the undesired effects of high shear forces that predisposes the red blood cells to mechanical hemolysis using the evacuated receptacle as a means of blood specimen extraction.
 2. The construction according to claim 1 wherein the said hub means is made of metal.
 3. The construction according to claim 1 wherein the said hub means is made of rigid transparent plastic so as to allow visibility of the passage of blood intO the said fore cavity from the venous side as a positive indicating means favorable for the operator before prematurely communicating the valuable vacuum of the said evacuated specimen collection receptacle with the said assembly; such visibility through the structure of the said hub means also providing an accurate checking means for the operator in observing the functional property of the said valve in inhibiting blood flow across said valve when no evacuated specimen collection receptacle is installed with the said assembly as well as in observing the blood transfer across said valve''s open port from the said first cavity into the said second cavity as soon as a potent evacuated specimen collection receptacle has been properly linked with the said assembly.
 4. The construction according to claim 1 wherein the pointed end of said first hollow cannula has a bevel.
 5. The construction according to claim 1 wherein the pointed end of said second hollow cannula has a bevel.
 6. The construction according to claim 1 wherein the said hub means is made of two pre-fabricated longitudinal halves strongly fused together along their pre-set alignable borders.
 7. The construction according to claim 1 wherein the said hub means is made of two pre-fabricated cross sectional halves strongly fused together by sonic technique of plastic fusion along the said pre-fabricated halves'' pre-set alignable borders.
 8. The construction according to claim 1 wherein the said hub means is partly made of transparent rigid plastic material surrounding the said first cavity, and said hub means partly made of non-transparent material surrounding the said second cavity.
 9. The construction according to claim 1 wherein the said valve is provided with a pin-hole at the said valve''s center so as to allow easy passage of air molecules from the said first cavity into the said second cavity as blood from the venous side is transported into the said front cavity via the said hollow cannula.
 10. A blood collection device having a rigid, hollow hub means, a first hollow cannula having a pointed end for the purpose of puncturing the skin and the blood vessel wall, a second hollow cannula having a pointed end for the purpose of piercing the rubber stopper of a potent evacuated specimen collection tube, first and second cavities in said hub means with a resilient valve situated therebetween, said first and second cannulas separated by the said first and second cavities as well as by the said valve, said first and second cavities including said valve found within the inner framework of said hub means which is made out of two pre-fabricated hub parts fused tightly and strongly together around their respective alignable rim, said first and second cavities respectively having a fluid inlet and a fluid outlet and also respectively communicating with the bore of the said first hollow cannula and with the bore of the said second hollow cannula, said valve held in stationary position therearound its outer border by the inner structure of the said fused hub means, said valve having at least a pair of equally dimensional slits running across the said valve center, and, in cross-section, said valve having the outer portion the thickest surrounding a thinner inner section including a particularly thinnest control part thereby structurally enhancing better reactive sensitivity of the said valve to the pre-calculated pertinent pressure differential changes at and immediately surrounding the said central part of the said valve, said valve in cross-section defining an inclined arc-like convexity toward said first cavity at its foreface proximal to the said first cavity, and said valve in cross-section describing an inclined arc-like concave configuration toward said second cavity at its hind face proximal to the said second cavity, and jointly both said inclined arc-like convexity and concave configuration being structurally formed from the outer part of the said valve toward the said valve central Part and being tapered toward its center, said valve capable of attaining three positions, a normally closed position, a minutely semi-open position, and an open position, said normally closed position being achieved when the said device is not in use and when the said second hollow cannula is not properly engaged with a potent aspirating evacuated specimen collection receptacle and the said first hollow cannula is not correctly linked with a potent, good sized vein, said minutely semi-open position achievable during displacement of air from the said first cavity into the said second cavity due to the entrance of the viscous blood from the venous side after the said first cavity lets the more positively pressured blood from the said venous side enter side and said first cavity''s lesser-positive pressured previously air-filled space when the said first hollow cannula with its pointed end establishes proper fluid communication with an active good sized vein and while the said second hollow cannula with its pointed end has not yet made the penetration through the rubber stopper of a potent evacuated specimen collection receptacle and therefore has not yet linked the vacuum of the said evacuated rectptacle with the said device, the open position of the said valve achievable as soon as the vacuum of the said evacuated receptacle has been linked with the said device wherein the said second hollow cannula with its pointed end has made the correct penetration through the rubber stopper of the said evccuated recptacle while the said second hollow cannula with it pointed end being already linked with the properly penetrated active vein, said valve being capable of achieving gradations in aperture sizes in direct proportion to the degree of pressure differential between the said venous blood source and the vacuum of the said evacuated receptacle thereby favoring the decrease in occurrence of mechanical hemolysis by reducing the ill effects of high shear forces upon the flowing red blood cells during the aspiration phase.
 11. The construction according to claim 10 wherein the hub means is made of rigid clear plastic material to allow visibility through the said hub means.
 12. The construction according to claim 10 wherein the hub means is made of metal.
 13. The construction according to claim 10 wherein the said hub means is made partly transparent surrounding the said first cavity, and said hub means made partly non-transparent surrounding the said second cavity.
 14. The construction according to claim 10 wherein the pointed end of said frist hollow cannula has a bevel.
 15. The construction according to claim 10 wherein the said second hollow cannula is provided with at least one lateral opening.
 16. The construction according to claim 10 wherein the pointed end of said second hollow cannula has a bevel.
 17. The construction according to claim 10 wherein the said hub means is made of two pre-fabricated longitudinal halves.
 18. The constructin according to claim 10 wherein the said hub means is made of fused cross-sectional halves.
 19. The construction according to claim 10 wherein the said device is effectively utilizable in both the singular sampling and poly-sampling of blood specimen from the vein without resulting in messy blood drip into the ambient environment.
 20. An effective hypodermic needle asembly applicable for use in both singular sampling and poly-sampling of blood specimen from the vein utilizing the evacuated specimen collection tube, firstly for the purpose of preventing the messy blood drip into the ambient environment during the process of blood extraction, secondly for the purpose of diminishing the mechanical hemolyzing effects of high shear forces upon the flowing red blood cells during the aspiration phase, and thirdly for the purpose of preventing the undesired premature exposure of the vacuum of the evacuated specimen collection tube; said assembly comprising, in combination, a rigid, hollow hub means internally having first and second chambers that are axially aligned with each other, a resilient valve therebetween said first and second chambers, a first hollow cannula with a pointed end for the purpose of puncturing the skin and the blood vessel wall, said first cannula axially fixed at its other end by a first section of the said hub means, said first cannula having communication with the said first chamber thereby providing a fluid inlet, a second hollow cannula with a pointed end for the purpose of piercing the diaphragm of the rubber stopper of the evacuated specimen collection tube, said second cannula axially fixed at its other end by a second section of the said hub means, said second cannula having communication with the said second chamber thereby providing a fluid outlet, said valve having a cross-section that is thickest at the outward portion and thinner at the inner portion and particularly thinnest at the central part making the said valve structurally sensitive to the relevant pressure differential changes focussed at and immediately around the said central part of the said valve; said valve in cross-section describing an inclined arc-like convexity toward said first chamber at its foreface proximal to the said first chamber, and, said valve in cross-section defining an inclined arc-like concavity toward said second chamber at its hind-face proximal to the said second chamber, the combination of the two said inclined arc-like convexity and concavity being formed from the outer section of the said valve toward the said valve''s central part and being tapered toward the said valve''s center, said valve provided with at least two equidistantly dimensioned centerly criss-crossing slits cutting the central part of the said valve and forming at least four said inclined arc-like concavity and convexity portions; said valve held in stationary position at its outer border by the inner framework of the said hub means; said valve normally in the closed position when not in use and when no evacuated specimen collection tube is installed with the said assembly, but said valve responding to two sets of conditions, the first condition wherein the said valve responds by achieving a brief semi-open position during the initial entrance of the said pointed end of the said first hollow cannula inside the lumen of the penetrated active good-sized vein thus displacing the gaseous content previously occupying the said first chamber by the incoming viscous blood via the bore of the said first cannula, said gaseous content in the form of air passing through the minutely widened said slits of the said valve, the second condition wherein the said valve achieves a gradation of varying apertural sizes while the potent evacuated specimen collection tube is aspirating specimen from the already linked vein, said varying apertural sizes of the said valve directly proportional to the pressure differential between the venous side and the aspirating capacity of the vacuum of the said evacuated specimen collection tube per unit time; said hub made of transparent plastic material to allow visibility therethrough as a positive checking means to observe the functioning of the said valve relevant to the flow of blood firstly into the said fore chamber before linking the vacuum of the said evacuated specimen collection tube, and then to observe the facileness of the said valve in letting blood flow across its open port into the said aft chamber when the potent evacuated specimen collection tube has been installed with the said assembly linked with the said vein.
 21. The construction according to claim 20 wherein the pointed end of said first cannula has a bevel.
 22. The construction according to claim 20 wherein the pointed end of said second cannula has a bevel.
 23. The construction according to claim 20 wherein the said second cannula at least has one lateral opening near the pointed end of the said second cannula.
 24. The construction according to claim 20 wherein the said valvular slits are straight as viewed frOm the end view.
 25. The construction according to claim 20 wherein the said valvular slits are of curved configuration as viewed from the front view.
 26. The construction according to claim 20 wherein the said hub means is made of two pre-fabricated longitudinal halves fused firmly together along their alignable rims.
 27. The construction according to claim 20 wherein the said hub means is made of two pre-fabricated cross-sectional halves fused firmly together by sonic means along their alignable borders.
 28. In combination, a blood extraction device comprising a hollow hub means having first and second cavities interiorly and with a resilient valve situated therebetween said cavities, a first hollow bevel-ended cannula having fluid communication with the said first cavity providing an inlet, a second hollow bevel-ended cannula with fluid communication with the said second cavity providing an outlet, said first and second cannulas axially fixed at their other ends by the respective axially opposite portions of the said hub means, said valve having a central H-shaped slit cutting across the said valve''s thickness, said valve having a cross-section through the center of the H-shaped slit that is has been inserted.
 29. The construction according to claim 28 wherein the said hub means is made of transparent plastic.
 30. The construction according to claim 28 wherein the said hub means is made of two pre-fabricated longitudinal halves fused strongly together along their alignable margins.
 31. The construction according to claim 28 wherein the said hub means is made of two pre-fabricated cross-sectional halves fused together along their respective alignable borders. 